Intravascular stent

BACKGROUND OF THE INVENTION

The present invention relates to expandable endoprosthesis devices, generally known as stents, which are designed for implantation in a patient's body lumen, such as blood vessels to maintain the patency thereof. These devices are particularly useful in the treatment and repair of blood vessels after a stenosis has been compressed by percutaneous transluminal coronary angioplasty (PTCA), percutaneous transluminal angioplasty (PTA), or removed by atherectomy or other means.

Stents are generally cylindrically-shaped devices which function to hold open and sometimes expand a segment of a blood vessel or other lumen such as a coronary artery. They are particularly suitable for use to support the lumen or hold back a dissected arterial lining which can occlude the fluid passageway therethrough.

A variety of devices are known in the art for use as stents and have included a plastically deformable wire mesh in a variety of patterns that are expanded after being placed intraluminally on a balloon catheter; helically wound coiled springs manufactured from an expandable heat sensitive metal; and self-expanding stents inserted in a compressed state and shaped in a zigzag pattern. One of the difficulties encountered using prior art stents involved maintaining the radial rigidity needed to hold open a body lumen while at the same time maintaining the longitudinal flexibility of the stent to facilitate its delivery and accommodate the often tortuous path of the body lumen.

Another problem area has been the limited range of expandability. Certain prior art stents expand only to a limited degree due to the uneven stresses created upon the stents during radial expansion. This necessitates providing stents with a variety of diameters, thus increasing the cost of manufacture. Additionally, having a stent with a wider range of expandability allows the physician to redilate the stent if the original vessel size was miscalculated.

SUMMARY OF THE INVENTION

The present devices are directed to stents of enhanced longitudinal flexibility and configuration which permit the stents to expand radially to accommodate a greater number of different diameter vessels, both large and small, than heretofore was possible. The stents have greater flexibility along their longitudinal axis to facilitate delivery through tortuous body lumens, but remain highly stable when expanded radially, to maintain the patency of a body lumen such as an artery or other vessel when implanted therein. The unique patterns of the stents permit both greater longitudinal flexibility and enhanced radial expansibility and stability compared to prior stents.

Each of the different embodiments of stents of the present invention includes a plurality of adjacent cylindrical rings which are generally expandable in the radial direction and arranged in alignment along a longitudinal stent axis. The cylindrical rings are formed in a variety of serpentine wave patterns transverse to the longitudinal axis and contain a plurality of alternating peaks and valleys. At least one link extends between adjacent cylindrical rings and connects them to one another. These links insure minimal longitudinal contraction during radial expansion of the stent in the body vessel. The links can be positioned in differing configurations or patterns along the stent length to enhance stent retention and eliminate strut fractures.

The resulting stent structures are a series of radially expandable cylindrical rings that are spaced longitudinally close enough so that small dissections in the wall of a body lumen may be pressed back into position against the lumenal wall, but not so close as to compromise the longitudinal flexibility of the stent both when being negotiated through the body lumens in their unexpanded state and when expanded into position. The serpentine patterns allow for an even expansion around the circumference by accounting for the relative differences in stress created by the radial expansion of cylindrical rings.

Each of the stents of the present invention can be readily delivered to the desired lumenal location by mounting it on an expandable member, such as a balloon, of a delivery catheter and passing the catheter-stent assembly through the body lumen to the implantation site. A variety of means for securing the stents to the expandable member of the catheter for delivery to the desired location are available. It is presently preferred to compress or crimp the stent onto the unexpanded balloon. Other means to secure the stent to the balloon include providing ridges or collars on the inflatable member to restrain lateral movement, using bioabsorbable temporary adhesives, or adding a retractable sheath to cover the stent during delivery through a body lumen.

The present stent structure is configured to optimize stent strength by varying the strut geometry along the length of the stent. By making the stent stronger or weaker in different regions of the stent, the properties can be customized to a particular application. The stent properties that could be altered include, but are not limited to, the width of each strut, and/or the length each cylindrical ring at a constant strut radial thickness.

The variation of the strength of the stent affects the manner in which the stent expands. As expected, the wider struts tend not to deform as easily as the narrower struts during expansion, while the longer struts within the longer cylindrical rings are better adapted to deployment in larger diameter vessels. On the other hand, an area with shorter and wider struts in the cylindrical rings tends to have greater radial strength than an area with longer and narrower struts in the cylindrical rings, given both areas having the same surface area.

Other features and advantages of the present invention will become more apparent from the following detailed description of the invention, when taken in conjunction with the accompanying exemplary drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

<figref idrefs="DRAWINGS">FIG. 1</figref> is an elevational view, partially in section, depicting a stent mounted on a delivery catheter disposed within a vessel.

<figref idrefs="DRAWINGS">FIG. 2</figref> is an elevational view, partially in section, similar to the stent of <figref idrefs="DRAWINGS">FIG. 1</figref> wherein the stent is expanded within a vessel.

<figref idrefs="DRAWINGS">FIG. 3</figref> is an elevational view, partially in section, showing the stent of <figref idrefs="DRAWINGS">FIG. 1</figref> expanded within the vessel after withdrawal of the delivery catheter.

<figref idrefs="DRAWINGS">FIG. 4A</figref> is a plan view depicting one embodiment of the stent in a flattened configuration and illustrating the differences between the end rings and the body rings.

<figref idrefs="DRAWINGS">FIG. 4B</figref> is a perspective view of the stent of <figref idrefs="DRAWINGS">FIG. 4A</figref> in a tubular configuration.

<figref idrefs="DRAWINGS">FIG. 5</figref> is a plan view of the stent of <figref idrefs="DRAWINGS">FIG. 4A</figref> showing the link pattern between the end rings and the body rings.

<figref idrefs="DRAWINGS">FIG. 6</figref> is a schematic depicting the circumferential relationship of the links along the stent longitudinal axis of the stent of <figref idrefs="DRAWINGS">FIG. 5</figref>.

<figref idrefs="DRAWINGS">FIG. 7</figref> is a partial plan view of the stent of <figref idrefs="DRAWINGS">FIG. 4A</figref> depicting the dimensions of the end rings, body rings and links.

<figref idrefs="DRAWINGS">FIG. 8A</figref> is a plan view of one embodiment of the stent of the present invention in a flattened configuration depicting the various rings and links.

<figref idrefs="DRAWINGS">FIG. 8B</figref> is a perspective view of the stent of <figref idrefs="DRAWINGS">FIG. 8A</figref> in a tubular configuration.

<figref idrefs="DRAWINGS">FIG. 9</figref> is a plan view of the stent of <figref idrefs="DRAWINGS">FIG. 8A</figref> depicting the link pattern.

<figref idrefs="DRAWINGS">FIG. 10</figref> is a schematic of the link pattern depicted in <figref idrefs="DRAWINGS">FIG. 9</figref> showing the circumferential relationship of the links along the stent longitudinal axis.

<figref idrefs="DRAWINGS">FIG. 11</figref> is a partial plan view of the stent of <figref idrefs="DRAWINGS">FIG. 8A</figref> depicting the dimensions of the end ring and several body rings.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Prior art stent designs, such as the MultiLink Stent™ manufactured by Advanced Cardiovascular Systems, Inc., Santa Clara, Calif., include plurality of cylindrical rings that are connected by three connecting members between adjacent cylindrical rings. Each of the cylindrical rings is formed of a repeating pattern of U-, Y-, and W-shaped members, typically having three repeating patterns forming each cylindrical ring. A more detailed discussion of the configuration of the MultiLink Stent™ can be found in U.S. Pat. No. 5,569,295 (Lam) and U.S. Pat. No. 5,514,154 (Lau et al.), whose contents are hereby incorporated by reference.

The present invention stent is shown in <figref idrefs="DRAWINGS">FIG. 1</figref>, where stent <b>10</b> is mounted onto delivery catheter <b>11</b>. Stent <b>10</b> generally includes a plurality of radially expandable cylindrical rings <b>12</b> disposed generally coaxially and interconnected by links <b>13</b> disposed between adjacent cylindrical rings <b>12</b>. The delivery catheter <b>11</b> has an expandable portion or balloon <b>14</b> for expanding stent <b>10</b> within artery <b>15</b> or other vessel.

The delivery catheter <b>11</b> onto which stent <b>10</b> is mounted is similar to a conventional balloon dilatation catheter for angioplasty procedures. The balloon <b>14</b> may be formed of suitable materials such as polyethylene, polyethylene terephthalate, polyvinyl chloride, nylon and, ionomers such as Surlyn® manufactured by the Polymer Products Division of the DuPont Company. Other polymers also may be used.

In order for stent <b>10</b> to remain in place on balloon <b>14</b> during delivery to the artery <b>15</b>, stent <b>10</b> is compressed or crimped onto balloon <b>14</b>.

The delivery of stent <b>10</b> to a coronary artery for example, is accomplished in the following manner. Stent <b>10</b> is first mounted onto inflatable balloon <b>14</b> on the distal extremity of delivery catheter <b>11</b>. Stent <b>10</b> may be crimped down onto balloon <b>14</b> to obtain a low profile. The catheter-stent assembly can be introduced within the patient's vasculature in a conventional technique through a guiding catheter (not shown). Guidewire <b>18</b> is disposed through the arterial section. The catheter-stent assembly is then advanced over guidewire <b>18</b> within artery <b>15</b>. Balloon <b>14</b> of catheter <b>11</b> is inflated or expanded, thus expanding stent <b>10</b> against the inside of artery <b>15</b>, which is illustrated in <figref idrefs="DRAWINGS">FIG. 2</figref>. While not shown in the drawing, artery <b>15</b> is preferably expanded slightly by the expansion of stent <b>10</b> to seat or otherwise embed stent <b>10</b> to prevent movement. Indeed, in some circumstances during the treatment of stenotic portions of an artery, the artery may have to be expanded considerably in order to facilitate passage of blood or other fluid therethrough.

In general, stent <b>10</b> serves to hold open artery <b>15</b> after catheter <b>11</b> is withdrawn, as illustrated in <figref idrefs="DRAWINGS">FIG. 3</figref>. Due to the formation of stent <b>10</b> from an elongated tubular member, the undulating component of the cylindrical elements of stent <b>10</b> is relatively flat in a transverse cross-section so that when stent <b>10</b> is expanded, cylindrical rings <b>12</b> are pressed into the wall of artery <b>15</b>. Cylindrical rings <b>12</b> of stent <b>10</b> that are pressed into the wall of artery <b>15</b> will eventually be covered with endothelial cell growth that further minimizes blood flow turbulence. The serpentine pattern of cylindrical rings <b>12</b> provide good tacking characteristics to prevent stent movement within the artery.

In one embodiment, shown in <figref idrefs="DRAWINGS">FIGS. 4A-7</figref>, stent <b>10</b> includes a tubular body <b>20</b> having a first end ring <b>22</b> and a second end ring <b>24</b>. A number of body rings <b>26</b> are positioned between the first end ring and the second end ring. The first end ring and the second end ring each have a first length <b>28</b> and the body rings each have a second length <b>30</b>. The first end ring and the second end ring each are shorter than the body rings for several reasons. First, when the stent is expanded, the stent length, after expansion, remains substantially the same as that prior to expansion, which is desirable for positioning the stent at a precise location in artery <b>15</b>. By maintaining the overall stent length during expansion there is minimal trauma or injury to the artery in the axial direction from the radial expansion of the stent rings. Secondly, there is a greater gap between the rings which allows the balloon to expand into the stent more during the heat and pressure process performed after the stent has been crimped on the balloon, which improves stent retention on the balloon during delivery.

All of the rings are positioned in an out-of-phase relationship and are connected by links. The first end ring <b>22</b> and the second end ring <b>24</b> each are connected to adjacent body rings by first links <b>32</b>. The links extend from a peak <b>40</b> of the first end ring to a peak <b>42</b> of the adjacent body ring. Likewise, the links extend from peaks <b>40</b> of the second end ring to the peaks <b>42</b> on an adjacent body ring. Similarly, each of the body rings are attached to adjacent body rings by second links <b>34</b>. The second links extend from the peak <b>42</b> of one body ring to the adjacent peak <b>42</b> of an adjacent body ring. The first links have a first length <b>36</b> and the second links have a second length <b>38</b>, where the first length of the first links is greater than the second length of the second links.

The number of links between the first end ring <b>22</b> and the body ring <b>26</b>, and the second end ring <b>24</b> and the body ring can vary in order to vary the flexibility of stent <b>10</b>. In one embodiment, as shown in <figref idrefs="DRAWINGS">FIGS. 4A-7</figref>, there are two first links <b>32</b> between the end rings and the body rings. Further, there are two second links <b>34</b> between adjacent body rings. The flexibility of the stent also is affected by the spacing of the links circumferentially around tubular body <b>20</b>. For example, referring to <figref idrefs="DRAWINGS">FIGS. 5 and 6</figref>, the first links are separated by two peaks <b>40</b> on the end rings. As shown in <figref idrefs="DRAWINGS">FIG. 6</figref>, the position <b>32</b>A of first links <b>32</b> are shown being circumferentially spaced by approximately 120°. The second links <b>34</b>, which connect adjacent body rings <b>26</b>, are separated by one peak <b>42</b> on the body rings. Looking at the left side of <figref idrefs="DRAWINGS">FIG. 5</figref>, for example, the first links are separated from the second links of the adjacent body ring by one-and-one-half peaks of separation in one circumferential direction and one-and-one-half peaks separation in the opposite circumferential direction. Moving in an axial direction from the left side of <figref idrefs="DRAWINGS">FIG. 5</figref> toward the right side, the second links of one body ring are separated by two-and-one-half peaks <b>42</b> in one circumferential direction and one-and-one-half peaks in the opposite circumferential direction. There are several advantages to the link pattern shown in <figref idrefs="DRAWINGS">FIGS. 4A-7</figref>. First, with the second links <b>34</b> being side by side between adjacent body rings <b>26</b>, there is less strain on the links during bending since both links are close together. In other words, when the links are separated by three or four peaks, each link is under greater stress during bending than if two links were side by side. Accordingly, one preferred link pattern as disclosed provides the best bending fatigue resistance, the highest flexibility for the preferred stent, and provides the best stent retention on the balloon.

With reference to <figref idrefs="DRAWINGS">FIG. 7</figref>, the first end ring <b>22</b> and the second end ring <b>24</b> (not shown) each have first bar arms <b>46</b> have a first width. In one embodiment, the first bar arm width <b>48</b> is approximately 0.0065 inch. The body rings <b>26</b> have second bar arms <b>50</b> having a second width <b>52</b>. The width of the second bar arms is approximately 0.0058 inch. Thus, the first bar arms width of 0.0065 inch is greater than the second width of second bar arms of approximately 0.0058 inch. There are several reasons why the end ring bar arms are wider than the body bar arms. First, there is improved stent retention because of better crimping with end rings having wider bar arms since there is less of a tendency for the ends to flare during delivery. The less tendency to flare also reduces strut fractures due to bending fatigue. Also, the shorter, wider bar arms on the end rings have higher radial strength than relatively longer and narrower bar arms. Further, the first end ring <b>22</b> and the second end ring <b>24</b> are shorter than the body rings <b>26</b>, so in order to keep the surface area of the end rings the same as the surface area of the body rings, the end rings have wider bar arms. There is less than one percent difference in overall surface area between, for example, first end ring <b>22</b> and any of the body rings <b>26</b>. Likewise, there is less than one percent difference in surface area between the surface area of second end ring <b>24</b> and any of body rings <b>26</b>. In maintaining the surface area among the rings relatively equal, when a drug is applied to the rings, the amount of drug delivered along the length of the stent is more consistent when the surface areas of the rings are substantially equal.

Again referring to <figref idrefs="DRAWINGS">FIG. 7</figref>, the first end ring <b>22</b> and the second end ring <b>24</b> have a number of peaks <b>40</b> which have first widths <b>54</b>, that width being approximately 0.0046 inch in one embodiment. The body rings <b>26</b> have peaks <b>42</b> that have second widths <b>56</b>, the second width being approximately 0.0038 inch in one embodiment. The first width <b>54</b> of the end ring peaks is wider than the second widths <b>56</b> of the body ring peaks <b>42</b> for substantially the same reasons as stated with respect to the difference in the bar arms widths of the end rings and the body rings.

Referring still to <figref idrefs="DRAWINGS">FIG. 7</figref>, the first links <b>32</b>, which extend between the end rings <b>22</b>,<b>24</b> and the body rings <b>26</b>, have a first width <b>58</b> of approximately 0.0042 inch, and a first length <b>36</b> of approximately 0.0149 inch. In contrast, the second links <b>34</b>, which connect adjacent body rings, have a second width <b>60</b> of approximately 0.0042 inch, however, the second links are approximately 0.0081 inch in length <b>38</b>, which is shorter than the length of the first links. By making the first links longer than the second links, while maintaining the width of the links the same, optimum flexibility along the longitudinal axis of the stent is achieved and there is less than 1% difference in surface area between the body rings and end rings.

It is preferred that the stent <b>10</b> shown in <figref idrefs="DRAWINGS">FIGS. 4A-7</figref>, have a constant strut thickness. In one embodiment, the radial thickness of all of the rings and links is approximately 0.0051 inch. While this dimension can vary depending upon the particular application, the 0.0051 inch radial thickness provides optimum flexibility to the stent, conformability to the vessel upon expansion, optimum radiopacity for viewing using fluoroscopy or other means of viewing, and optimum hoop strength in holding the artery open after the stent has been expanded. In this embodiment, there are six peaks <b>40</b> in each end ring <b>22</b>,<b>24</b>, six peaks <b>42</b> for each body ring <b>26</b>, and the overall stent length is approximately 14 mm (0.5512 inch).

In another embodiment, shown in <figref idrefs="DRAWINGS">FIGS. 8A-11</figref>, stent <b>70</b> includes a tubular body <b>72</b> comprised of end rings <b>74</b> and body rings <b>76</b>. There are twelve rings in this embodiment and each ring has nine peaks. As will be further described, the end rings and the body rings have substantially the same dimensions, including overall length, shape, width of bar arms, and width of peaks. Thus, both the end rings and body rings have bar arms <b>78</b> that have a constant width of approximately 0.0047 inch. Likewise, the peaks <b>80</b> on the end rings and the body rings have a width of approximately 0.0034 inch. Multiple links <b>82</b> connect the end rings to the body rings and also connect adjacent body rings to each other, all of which connect at peaks <b>80</b>. As can be seen from the drawings, all of the rings are out of phase. The link width <b>84</b> and the link length <b>86</b> are uniform, wherein the width is approximately 0.0041 inch, and the link length is approximately 0.0042 inch. The length <b>88</b> of each ring is approximately 0.0606 inch for this embodiment where the overall stent length is 0.5512 inch. The radial thickness of the rings and links is substantially uniform and in this embodiment, is approximately 0.0053 inch. All of the foregoing dimensions and numbers of links and rings are exemplary and intended as one preferred embodiment. Other preferred embodiments may have different dimensions to suit a particular need.

In order to maximize flexibility, insure that the body of the stent does not turn oval, and the ends of the stent do not flare outwardly during delivery of the stent, the link pattern has been optimized, as can be seen in <figref idrefs="DRAWINGS">FIGS. 9 and 10</figref>. Thus, in this embodiment, three links <b>82</b> connect the end rings <b>74</b> to the adjacent body rings <b>76</b> while two links connect adjacent body rings to each other. The three links are positioned <b>82</b>A between the end rings and the body rings are 120° apart as can be seen in <figref idrefs="DRAWINGS">FIG. 10</figref>. The two links joining adjacent body rings are positioned <b>82</b>B approximately 80° apart as can be seen in <figref idrefs="DRAWINGS">FIG. 10</figref>. Moving from the left side of <figref idrefs="DRAWINGS">FIG. 9</figref> or <figref idrefs="DRAWINGS">FIG. 10</figref> toward the right side, the links <b>82</b> joining adjacent body rings have a pattern where the links are separated by two peaks <b>80</b>, and by seven peaks in the next adjacent set of rings, and then back to two peaks in the next set of adjacent rings toward the right. When viewing <figref idrefs="DRAWINGS">FIG. 10</figref>, it is clear that the two links joining the adjacent body rings all are separated circumferentially by two peaks <b>80</b> in one circumferential direction, and seven peaks <b>80</b> in the opposite circumferential direction. This link pattern provides optimal flexibility and security along the longitudinal axis of the stent and also imparts less strain on the links during bending since the links are relatively close together, being separated by only two peaks <b>80</b>, so that there is less bending stress on each individual link when they are closer together. In this embodiment, there are nine peaks <b>80</b> in each of the end rings <b>74</b> and body rings <b>76</b>, and the overall stent length is 14 mm (0.5512 inch).

One important feature of all of the embodiments of the present invention is the capability of the stents to expand from a low-profile diameter to a diameter much greater than heretofore was available, while still maintaining structural integrity in the expanded state and remaining highly flexible. Due to the novel structures, the stents of the present invention can have an overall expansion ratio of about 1.0 up to about 4.0 times the original diameter, or more, using certain compositions of stainless steel. For example, a 316L stainless steel stent of the invention can be radially expanded from a diameter of 1.0 unit up to a diameter of about 4.0 units, which deforms the structural members beyond the elastic limit. The stents still retain structural integrity in the expanded state and will serve to hold open the vessel in which they are implanted. Materials other than stainless steel (316L) may afford higher or lower expansion ratios without sacrificing structural integrity.

The stents of the present invention can be made in many ways. However, the preferred method of making the stent is to cut a thin-walled tubular member, such as a stainless steel tubing, to remove portions of the tubing in the desired pattern for the stent, leaving relatively untouched the portions of the metallic tubing which are to form the stent. It is preferred to cut the tubing in the desired pattern by means of a machine-controlled laser which is well known in the art.

The stent tubing may be made of a suitable biocompatible material such as stainless steel, titanium, cobalt-chromium, tantalum, super-elastic (nickel-titanium) NiTi alloys and even high strength thermoplastic polymers. When stainless steel is utilized, the stainless steel can be annealed and one-eighth hardened. The stent diameters are very small, so the tubing from which it is made must necessarily also have a small diameter. For stents implanted in other body lumens, such as PTA applications, the dimensions of the tubing are correspondingly larger. The diameters and tubing wall thickness of the stents can vary according to a particular application and are known in the art. While it is preferred that the stents be made from laser cut tubing, those skilled in the art will realize that the stent can be laser cut from a flat sheet and then rolled up in a cylindrical configuration with the longitudinal edges welded to form a cylindrical member.

In the instance when the stents are made from plastic, the implanted stent may have to be heated within the arterial site where the stent is expanded to facilitate the expansion of the stent. Once expanded, it would then be cooled to retain its expanded state. The stent may be conveniently heated by heating the fluid within the balloon or the balloon itself directly by a known method.

The stents may also be made of materials such as superelastic (sometimes called pseudo-elastic) nickel-titanium (NiTi) alloys. In this case, the stent would be formed full size but deformed (e.g. compressed) to a smaller diameter onto the delivery catheter to facilitate intraluminal delivery to a desired intraluminal site. The stress induced by the deformation transforms the stent from an austenite phase to a martensite phase, and upon release of the force when the stent reaches the desired intraluminal location, allows the stent to expand due to the transformation back to the more stable austenite phase. Further details of how NiTi superelastic alloys operate can be found in U.S. Pat. No. 4,665,906 (Jervis) and U.S. Pat. No. 5,067,957 (Jervis), incorporated herein by reference.

The present invention stent is ideally suited for drug delivery (i.e., delivery of a therapeutic agent) since it has a uniform surface area which ensures uniform distribution of drugs. Typically, a polymer is coated onto the stent of the type disclosed in U.S. Pat. Nos. 6,824,559 and 6,783,793 which are incorporated herein by reference.

These bioactive agents can be any agent, which is a therapeutic, prophylactic, or diagnostic agent. These agents can have anti-proliferative or anti-inflammmatory properties or can have other properties such as antineoplastic, antiplatelet, anti-coagulant, anti-fibrin, antithrombonic, antimitotic, antibiotic, antiallergic, antioxidant as well as cystostatic agents. Examples of suitable therapeutic and prophylactic agents include synthetic inorganic and organic compounds, proteins and peptides, polysaccharides and other sugars, lipids, and DNA and RNA nucleic acid sequences having therapeutic, prophylactic or diagnostic activities. Nucleic acid sequences include genes, antisense molecules which bind to complementary DNA to inhibit transcription, and ribozymes. Some other examples of other bioactive agents include antibodies, receptor ligands, enzymes, adhesion peptides, blood clotting factors, inhibitors or clot dissolving agents such as streptokinase and tissue plasminogen activator, antigens for immunization, hormones and growth factors, oligonucleotides such as antisense oligonucleotides and ribozymes and retroviral vectors for use in gene therapy. Examples of anti-proliferative agents include rapamycin and its functional or structural derivatives, 40-O-(2-hydroxy)ethyl-rapamycin (everolimus), and its functional or structural derivatives, paclitaxel and its functional and structural derivatives. Examples of rapamycin derivatives include methyl rapamycin, ABT-578, 40-O-(3-hydroxy)propyl-rapamycin, 40-O-[2-(2-hydroxy)ethoxy]ethyl-rapamycin, and 40-O-tetrazole-rapamycin. Examples of paclitaxel derivatives include docetaxel. Examples of antineoplastics and/or antimitotics include methotrexate, azathioprine, vincristine, vinblastine, fluorouracil, doxorubicin hydrochloride (e.g. Adriamycin® from Pharmacia &amp; Upjohn, Peapack N.J.), and mitomycin (e.g. Mutamycin® from Bristol-Myers Squibb Co., Stamford, Conn.). Examples of such antiplatelets, anticoagulants, antifibrin, and antithrombins include sodium heparin, low molecular weight heparins, heparinoids, hirudin, argatroban, forskolin, vapiprost, prostacyclin and prostacyclin analogues, dextran, D-phe-pro-arg-chloromethylketone (synthetic antithrombin), dipyridamole, glycoprotein IIb/IIIa platelet membrane receptor antagonist antibody, recombinant hirudin, thrombin inhibitors such as Angiomax ä (Biogen, Inc., Cambridge, Mass.), calcium channel blockers (such as nifedipine), colchicine, fibroblast growth factor (FGF) antagonists, fish oil (omega 3-fatty acid), histamine antagonists, lovastatin (an inhibitor of HMG-CoA reductase, a cholesterol lowering drug, brand name Mevacor® from Merck &amp; Co., Inc., Whitehouse Station, N.J.), monoclonal antibodies (such as those specific for Platelet-Derived Growth Factor (PDGF) receptors), nitroprusside, phosphodiesterase inhibitors, prostaglandin inhibitors, suramin, serotonin blockers, steroids, thioprotease inhibitors, triazolopyrimidine (a PDGF antagonist), nitric oxide or nitric oxide donors, super oxide dismutases, super oxide dismutase mimetic, 4-amino-2,2,6,6-tetramethylpiperidine-1-oxyl (4-amino-TEMPO), estradiol, anticancer agents, dietary supplements such as various vitamins, and a combination thereof. Examples of anti-inflammatory agents including steroidal and non-steroidal anti-inflammatory agents include tacrolimus, dexamethasone, clobetasol, combinations thereof. Examples of such cytostatic substance include angiopeptin, angiotensin converting enzyme inhibitors such as captopril (e.g. Capoten® and Capozide® from Bristol-Myers Squibb Co., Stamford, Conn.), cilazapril or lisinopril (e.g. Prinivil® and Prinzide® from Merck &amp; Co., Inc., Whitehouse Station, N.J.). An example of an antiallergic agent is permirolast potassium. Other therapeutic substances or agents which may be appropriate include alpha-interferon, bioactive RGD, and genetically engineered epithelial cells. The foregoing substances can also be used in the form of prodrugs or co-drugs thereof. The bioactive agents also include metabolites of the foregoing substances and prodrugs of these metabolites. The foregoing substances are listed by way of example and are not meant to be limiting. Other active agents which are currently available or that may be developed in the future are equally applicable.

While the invention has been illustrated and described herein in terms of its use as intravascular stents, it will be apparent to those skilled in the art that the stents can be used in other instances in all vessels in the body. Since the stents of the present invention have the novel feature of expanding to very large diameters while retaining their structural integrity, they are particularly well suited for implantation in almost any vessel where such devices are used. This feature, coupled with limited longitudinal contraction of the stent when it is radially expanded, provides a highly desirable support member for all vessels in the body. Other modifications and improvements may be made without departing from the scope of the invention.